US4112522A - Knee-joint prosthesis - Google Patents
Knee-joint prosthesis Download PDFInfo
- Publication number
- US4112522A US4112522A US05/738,978 US73897876A US4112522A US 4112522 A US4112522 A US 4112522A US 73897876 A US73897876 A US 73897876A US 4112522 A US4112522 A US 4112522A
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- United States
- Prior art keywords
- flexing
- pivot
- rotation
- axis
- prosthesis
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
- 210000000629 knee joint Anatomy 0.000 title abstract description 4
- 229920003023 plastic Polymers 0.000 claims description 11
- 239000004033 plastic Substances 0.000 claims description 11
- 210000000988 bone and bone Anatomy 0.000 claims description 8
- 230000001419 dependent effect Effects 0.000 claims description 2
- 238000006073 displacement reaction Methods 0.000 claims 1
- 210000002303 tibia Anatomy 0.000 abstract description 21
- 210000000689 upper leg Anatomy 0.000 abstract description 19
- 229940025016 jointflex Drugs 0.000 abstract 1
- 210000003127 knee Anatomy 0.000 description 5
- 210000001699 lower leg Anatomy 0.000 description 4
- 239000002184 metal Substances 0.000 description 4
- 239000002639 bone cement Substances 0.000 description 3
- 210000004439 collateral ligament Anatomy 0.000 description 3
- 238000005299 abrasion Methods 0.000 description 2
- 238000002513 implantation Methods 0.000 description 2
- 238000002271 resection Methods 0.000 description 2
- 238000005452 bending Methods 0.000 description 1
- 238000010276 construction Methods 0.000 description 1
- 201000010099 disease Diseases 0.000 description 1
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 1
- 239000007943 implant Substances 0.000 description 1
- 210000003041 ligament Anatomy 0.000 description 1
- 238000011068 loading method Methods 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 230000000717 retained effect Effects 0.000 description 1
- 238000004088 simulation Methods 0.000 description 1
- 238000006467 substitution reaction Methods 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/38—Joints for elbows or knees
- A61F2/3836—Special connection between upper and lower leg, e.g. constrained
- A61F2/384—Special connection between upper and lower leg, e.g. constrained hinged, i.e. with transverse axle restricting the movement
Definitions
- the invention relates to an endo knee prosthesis having a femur part and a tibia part which are adapted to be anchored, each by way of an intramedullary stem, in the femur and lower leg bone respectively and which are pivotable relatively to one another around a flexing-axis pin to an extent limited by abutments.
- German patent specification No. 2 114 287 proposes that the joint zone of the prosthesis be so narrow that the joint can be implanted inside the femoral head. This step really does obviate the difficulties mentioned by making total resection of the condyle unnecessary. Also, implanting the prosthesis in a recessed part of the condyle provides extra securing against turning. Unfortunately, with the known joint construction two disadvantages arise, for the reason that the prosthesis must be taken apart for implantation and, after the intramedullary stems have been positioned, the prosthesis must be assembled by way of the hinge or pivot pin.
- a pivot is fixedly disposed on the tibia or femur part, extends along the longitudinal axis of the tibia part and prolongs whichever part is connected to it towards the other part; and the femur or tibia part is formed with a bore which is adapted to receive the pivot, there being disposed on the last-mentioned part a securing element for securing the pivot in the bore.
- the femur part is articulated via the flexing-axis pin to an intermediate element which is formed with the pivot-receiving bore and which is so connected via the pivot to the tibia part as to be rotatable, to an extent limited by abutments dependent upon the flexing angle, and releasable. Consequently, and in contrast to the prior art, mobility of the joint is assured not only around the horizontal flexing axis but also around a substantially vertical pivoting axis; there is therefore complete simulation of the natural joint which, when the lower leg bone moves from the extended into the flexed position, permits rotation of the lower leg bone relatively to the femur as well as the bending movement. In both the natural joint and in this further development of the prosthesis according to the invention the amount of pivoting depends upon the angle between the femur and the lower leg bone.
- the body of rotation is an adjustable eccentric connected to the flexing-axis pin and the flexing-axis pin is mounted relatively to the femur part and intermediate element, and the latter is mounted relatively to the pivot, its bottom part and a bearing surface of the tibia part, in each case by means of at least one plastics bearing element; the plastics bearing elements can be replaceable.
- the eccentric and that part of the pivot which is near the eccentric are enclosed in dust-tight manner, and the securing element is a screw which is preferably self-locking, is screwed into a projection of the intermediate element and engages at its exposed end in an annular groove in the pivot or the bottom part thereof.
- FIG. 1 is an end view of the endo knee prosthesis in its extended position
- FIG. 2 is a side view of the prosthesis of FIG. 1;
- FIG. 3 is a view to an enlarged scale and in section on the line 3--3 of FIG. 1, and
- FIG. 4 is a section through the prosthesis on the line 4--4 of FIG. 3 but with the joint flexed.
- An implant endo knee prosthesis to be described hereinafter is subdivided into a femur part F, an intermediate member Z and a tibia part T, and make a hinging movement around a flexing axis 15 between -5° and +145° and also, when flexed, is adapted to make a limited rotation of the order of something like ⁇ 20° around the axis of the tibia.
- the joint embodying the flexing axis is disposed already made up between the femur part F and the intermediate element Z, whereas the rotational bearing is provided between the element Z and the tibia part T and, as will become apparent from the following description, is assembled in the course of the surgical operation.
- the femur part F has an intramedullary stem 10 and a fork 12 which, in the view in side elevation in FIG. 2, engages around the flexing axis 15 like a circle segment; the fork 12 is so recessed at its centre and transversely of the axis 15 that two fork arms 12a, 12b arise.
- the two arms 12a, 12b are formed concentrically of the axis 15 with a bore 14.
- the intermediate element Z has a lug 30 which is introducible into the recess of the fork 12 and whose outer periphery is rounded around the axis 15 with the same radius as is the fork 12.
- a central bore which extends coaxially of the axis 15 and through the lug 30 has a diameter greater than the diameter of the bore 14 by an extent such that the difference between the two diameters allows sufficient space to receive a plastics bearing element subdivided into two bearing parts or shells 17, 18 (see FIG. 4).
- the two parts 17, 18 are introduced into the central bore of lug 30.
- Each part 17, 18 has a side flange.
- the intermediate element Z then has its lug 30 pushed into the recess of the fork 12 of the femur part F and is secured non-rotatably by the introduction of a flexing-axis pin 20.
- the lug 30 is connected via a relatively narrow neck 32 to a circular base 34 whose underside is a base surface 35 adapted to absorb the vertical forces arising in subsequent use.
- the pin 20 is secured against turning and sliding out laterally by means of two screwthreaded pins 27 screwed into corresponding bores in the fork arms 12a, 12b.
- the pin 20 takes the form of an eccentric 22 having an eccentric axis 23.
- eccentric 22 i.e., the position of its axis 23 -- relatively to the flexing axis 15 is a matter of considerable importance in assembly.
- a plastics runner 36 pushed over neck 32 of element Z is adapted in its curved outer diameter to the fork 12 and also, as can be gathered from FIGS. 2 and 3, is rounded at both ends.
- the rounded ends serve as resilient abutments limiting the hinging movement of the prosthesis around the flexing axis 15; as previously stated, in the present embodiment the hinging movement can extend over a region of from -5° to +145°.
- the range of hinging movement can be varied readily by using a differently shaped runner 36.
- a plastics bearing element 38 By way of a plastics bearing element 38 the surface 35 bears rotatably on a correspondingly shaped end plate 40 of the tibia part T.
- a pivot 42 having a circular base 43 rises from the centre of end plate 40 and serves to centre the intermediate element Z, the same having provision for limited rotation relatively to the tibia part T.
- the elements 40, 43, 42 are disposed concentrically of a pivot axis 50 which corresponds to the tibia axis and which, as can be seen in FIGS. 3 and 4, is offset from the flexing axis 15; the axis 50 intersects a horizontal (in FIG. 3) axis passing through the flexing axis 15 at right angles.
- the plastics bearing element 38 separating surface 35 of element Z from the tibia part end plate 40 has a stepped sleeve-like extension which engages intimately around the outer contours of the pivot pin 42 and base 43 and which is preassembled in the combination of the intermediate element Z and the femur part F.
- the stepped extension is received in a corresponding recess in the element Z and retained by a screw 46 screwed into a tapped bore in a projection 33 of neck 32.
- the exposed end of screw 46 extends through a lateral bore of bearing element 38, the main function of screw 46 being to serve as a releasable connecting element between the members Z and T.
- the exposed end of screw 46 engages in an annular groove 44 in base 43.
- all that the operating surgeon has to do is to connect the tibia part T to the intermediate element Z by pushing pivot pin 42 with base 43 into the corresponding recess of the bearing element 38 and tightening the screw 46.
- the length thereof is such that when its head is in contact with the outside surface of projection 33, the free end of the screw engages in groove 44 but does not contact the base thereof. This ensures that the tibia part T remains rotatable relatively to the intermediate element Z.
- the top end of the member 42 is formed on one side with a recess 45 to provide a cooperating surface which, with the device assembled, is near eccentric 22 of flexing-axis pin 20.
- the recess 45 engages with the correspondingly adjusted eccentric 22 without clearance -- i.e., when the joint is in the extended position the tibia part T cannot rotate around the axis 50 relatively to the femur part F.
- the joint is flexed through e.g. 90° in the manner shown in FIG.
- the eccentric 22 and cooperating surface provided by recess 45 form an abduction and rotation abutment in which both permissable abduction and rotation of the joint are controlled by the abutment of the pin and pivot.
- the angle of rotation can be adapted to the rotatability when flexed of a natural knee joint by appropriate adjustment of the eccentric 22 and is somewhere around ⁇ 20°.
- All bearing areas of the endo knee prosthesis hereinbefore described are lined with an appropriate plastics ensuring freedom from wear and a long working life.
- the risk of metal abrasion is therefore completely obviated, and so there is no risk of metallosis.
- the only metal parts which engage directly with one another are the eccentric 22 and the surfaces of the recess 45. However, these metal parts are completely enclosed, and so any metal abrasion occurring cannot be washed out into the organism.
- the subassembly comprising the femur part F and intermediate element Z with the flexing joint, such unit being adapted to be implanted in the completely prefabricated state, is relatively narrow near the fork 12 and can be completely received in a prepared condylar cavity.
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- Health & Medical Sciences (AREA)
- Orthopedic Medicine & Surgery (AREA)
- Physical Education & Sports Medicine (AREA)
- Cardiology (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Transplantation (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Vascular Medicine (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Prostheses (AREA)
Abstract
A knee joint prosthesis has a femur part and a tibia part which are pivotable relative to one another about a joint-flexing axis. One of the parts is rotatable about an axis perpendicular to the flexing axis. An eccentric member, the angular position of which is determined by the degree of joint flex, engages a pair of abutments on the rotatable part so that rotation is only possible when the joint is flexed with the angle of rotation being determined by the size of the gap between the abutments and eccentric member when the joint is in its flexed position.
Description
The invention relates to an endo knee prosthesis having a femur part and a tibia part which are adapted to be anchored, each by way of an intramedullary stem, in the femur and lower leg bone respectively and which are pivotable relatively to one another around a flexing-axis pin to an extent limited by abutments.
When it becomes necessary to replace a knee joint by a prosthesis as a result of damage due to accident or disease, the operating surgeon will endeavor to resect as little bone as possible and to select a prosthesis which is likely to be highly durable, so that the operation does not have to be repeated and the joint does not stiffen.
In the case of conventional total prostheses, it has been necessary to resect the widened heads from the femur and tibia, whereafter the intramedullary stems on the hinge-like prosthesis are introduced into the medullary cavity of the associated bones and anchored in place by bone cement. Considerable resection is necessary in this procedure and durability is limited since all that secures the prosthesis from turning in the bones is just the bone cement. Consequently, impact torque loadings of the joint occasionally cause the prosthesis to loosen and the loosening is not only painful but makes a further operation necessary.
To obviate these problems, German patent specification No. 2 114 287 proposes that the joint zone of the prosthesis be so narrow that the joint can be implanted inside the femoral head. This step really does obviate the difficulties mentioned by making total resection of the condyle unnecessary. Also, implanting the prosthesis in a recessed part of the condyle provides extra securing against turning. Unfortunately, with the known joint construction two disadvantages arise, for the reason that the prosthesis must be taken apart for implantation and, after the intramedullary stems have been positioned, the prosthesis must be assembled by way of the hinge or pivot pin. Consequently, a bore or recess extending medially through the condyle is necessary for such pin, with a resultant reduction of the unresected part of the condyle. Yet another disadvantage is that for anatomical reasons the bore is required in a part of the condyle where the lateral ligaments are attached, so that such ligaments have to be removed, even though undamaged, and therefore become unavailable to damp forces and to provide additional guiding of the joint.
It is therefore an object of the invention so to improve the known prostheses that the lateral ligaments do not have to be touched in the implantation operation -- i.e., the lateral ligaments can continue to perform their functions after the substitution of the prosthesis for the natural joint.
According to the invention, therefore, in an endo knee prosthesis of the kind described a pivot is fixedly disposed on the tibia or femur part, extends along the longitudinal axis of the tibia part and prolongs whichever part is connected to it towards the other part; and the femur or tibia part is formed with a bore which is adapted to receive the pivot, there being disposed on the last-mentioned part a securing element for securing the pivot in the bore.
As a very advantageous development of such a prosthesis, the femur part is articulated via the flexing-axis pin to an intermediate element which is formed with the pivot-receiving bore and which is so connected via the pivot to the tibia part as to be rotatable, to an extent limited by abutments dependent upon the flexing angle, and releasable. Consequently, and in contrast to the prior art, mobility of the joint is assured not only around the horizontal flexing axis but also around a substantially vertical pivoting axis; there is therefore complete simulation of the natural joint which, when the lower leg bone moves from the extended into the flexed position, permits rotation of the lower leg bone relatively to the femur as well as the bending movement. In both the natural joint and in this further development of the prosthesis according to the invention the amount of pivoting depends upon the angle between the femur and the lower leg bone.
Preferably, the body of rotation is an adjustable eccentric connected to the flexing-axis pin and the flexing-axis pin is mounted relatively to the femur part and intermediate element, and the latter is mounted relatively to the pivot, its bottom part and a bearing surface of the tibia part, in each case by means of at least one plastics bearing element; the plastics bearing elements can be replaceable.
According to another feature of the invention, the eccentric and that part of the pivot which is near the eccentric are enclosed in dust-tight manner, and the securing element is a screw which is preferably self-locking, is screwed into a projection of the intermediate element and engages at its exposed end in an annular groove in the pivot or the bottom part thereof.
The invention will be described in greater detail hereinafter with reference to the preferred embodiment shown in the drawings wherein:
FIG. 1 is an end view of the endo knee prosthesis in its extended position;
FIG. 2 is a side view of the prosthesis of FIG. 1;
FIG. 3 is a view to an enlarged scale and in section on the line 3--3 of FIG. 1, and
FIG. 4 is a section through the prosthesis on the line 4--4 of FIG. 3 but with the joint flexed.
An implant endo knee prosthesis to be described hereinafter is subdivided into a femur part F, an intermediate member Z and a tibia part T, and make a hinging movement around a flexing axis 15 between -5° and +145° and also, when flexed, is adapted to make a limited rotation of the order of something like ±20° around the axis of the tibia. The joint embodying the flexing axis is disposed already made up between the femur part F and the intermediate element Z, whereas the rotational bearing is provided between the element Z and the tibia part T and, as will become apparent from the following description, is assembled in the course of the surgical operation.
The femur part F has an intramedullary stem 10 and a fork 12 which, in the view in side elevation in FIG. 2, engages around the flexing axis 15 like a circle segment; the fork 12 is so recessed at its centre and transversely of the axis 15 that two fork arms 12a, 12b arise. The two arms 12a, 12b are formed concentrically of the axis 15 with a bore 14.
The intermediate element Z has a lug 30 which is introducible into the recess of the fork 12 and whose outer periphery is rounded around the axis 15 with the same radius as is the fork 12. A central bore which extends coaxially of the axis 15 and through the lug 30 has a diameter greater than the diameter of the bore 14 by an extent such that the difference between the two diameters allows sufficient space to receive a plastics bearing element subdivided into two bearing parts or shells 17, 18 (see FIG. 4). At assembly the two parts 17, 18 are introduced into the central bore of lug 30. Each part 17, 18 has a side flange. The intermediate element Z then has its lug 30 pushed into the recess of the fork 12 of the femur part F and is secured non-rotatably by the introduction of a flexing-axis pin 20.
The lug 30 is connected via a relatively narrow neck 32 to a circular base 34 whose underside is a base surface 35 adapted to absorb the vertical forces arising in subsequent use.
As can be gathered from FIGS. 3 and 4, the pin 20 is secured against turning and sliding out laterally by means of two screwthreaded pins 27 screwed into corresponding bores in the fork arms 12a, 12b. At its centre the pin 20 takes the form of an eccentric 22 having an eccentric axis 23. As will be described in greater detail hereinafter, the position of eccentric 22 -- i.e., the position of its axis 23 -- relatively to the flexing axis 15 is a matter of considerable importance in assembly.
A plastics runner 36 pushed over neck 32 of element Z is adapted in its curved outer diameter to the fork 12 and also, as can be gathered from FIGS. 2 and 3, is rounded at both ends. The rounded ends serve as resilient abutments limiting the hinging movement of the prosthesis around the flexing axis 15; as previously stated, in the present embodiment the hinging movement can extend over a region of from -5° to +145°. The range of hinging movement can be varied readily by using a differently shaped runner 36.
By way of a plastics bearing element 38 the surface 35 bears rotatably on a correspondingly shaped end plate 40 of the tibia part T. A pivot 42 having a circular base 43 rises from the centre of end plate 40 and serves to centre the intermediate element Z, the same having provision for limited rotation relatively to the tibia part T. The elements 40, 43, 42 are disposed concentrically of a pivot axis 50 which corresponds to the tibia axis and which, as can be seen in FIGS. 3 and 4, is offset from the flexing axis 15; the axis 50 intersects a horizontal (in FIG. 3) axis passing through the flexing axis 15 at right angles.
As can be gathered from FIG. 3, the plastics bearing element 38 separating surface 35 of element Z from the tibia part end plate 40 has a stepped sleeve-like extension which engages intimately around the outer contours of the pivot pin 42 and base 43 and which is preassembled in the combination of the intermediate element Z and the femur part F. The stepped extension is received in a corresponding recess in the element Z and retained by a screw 46 screwed into a tapped bore in a projection 33 of neck 32. The exposed end of screw 46 extends through a lateral bore of bearing element 38, the main function of screw 46 being to serve as a releasable connecting element between the members Z and T. The exposed end of screw 46 engages in an annular groove 44 in base 43. After the femur part F and tibia part T have been introduced into appropriate cavities or recesses or the like in the femur and tibia and embedded with bone cement or the like, all that the operating surgeon has to do is to connect the tibia part T to the intermediate element Z by pushing pivot pin 42 with base 43 into the corresponding recess of the bearing element 38 and tightening the screw 46. The length thereof is such that when its head is in contact with the outside surface of projection 33, the free end of the screw engages in groove 44 but does not contact the base thereof. This ensures that the tibia part T remains rotatable relatively to the intermediate element Z.
As can be seen in FIGS. 3 and 4, the top end of the member 42 is formed on one side with a recess 45 to provide a cooperating surface which, with the device assembled, is near eccentric 22 of flexing-axis pin 20. When the prosthesis is in the extended position shown in FIG. 3, the recess 45 engages with the correspondingly adjusted eccentric 22 without clearance -- i.e., when the joint is in the extended position the tibia part T cannot rotate around the axis 50 relatively to the femur part F. However, when the joint is flexed through e.g. 90° in the manner shown in FIG. 4, there is a gap d between the eccentric 22 and the recess 45, the gap enabling the whole tibia part T to turn to either hand until the outside edges of recess 45 abut the eccentric 22. Thus, the eccentric 22 and cooperating surface provided by recess 45 form an abduction and rotation abutment in which both permissable abduction and rotation of the joint are controlled by the abutment of the pin and pivot. The angle of rotation can be adapted to the rotatability when flexed of a natural knee joint by appropriate adjustment of the eccentric 22 and is somewhere around ±20°.
All bearing areas of the endo knee prosthesis hereinbefore described are lined with an appropriate plastics ensuring freedom from wear and a long working life. The risk of metal abrasion is therefore completely obviated, and so there is no risk of metallosis. The only metal parts which engage directly with one another are the eccentric 22 and the surfaces of the recess 45. However, these metal parts are completely enclosed, and so any metal abrasion occurring cannot be washed out into the organism.
The subassembly comprising the femur part F and intermediate element Z with the flexing joint, such unit being adapted to be implanted in the completely prefabricated state, is relatively narrow near the fork 12 and can be completely received in a prepared condylar cavity.
Claims (10)
1. A joint prosthesis having a flexing-axis pin having a flexing axis, first and second parts which are adapted to be anchored in first and second bones, respectively, on opposite sides of said joint and which are pivotable through a range of flexing angle relative to one another about said flexing-axis pin, said joint prosthesis further comprising:
a pivot disposed on one of said first and second parts and extending along the longitudinal axis of that part on which it is disposed; and
an intermediate element having a pin receiving bore for receiving said flexing-axis pin, a pivot-receiving bore for receiving said pivot and a securing element for securing said pivot in said pivot-receiving bore, the central portion of said flexing-axis pin together with said pivot forming an abduction and rotation abutment in which the amount of permissible of rotation is dependent on the flexing angle.
2. A prosthesis according to claim 1, characterised in that the abduction and rotation abutment is formed by a body of rotation having an axis parallel to but offset from the flexing axis and by a cooperating surface on said pivot, the spacing between said body of rotation and said cooperating surface being determined by the flexing angle of said joint such that the body of rotation makes complete contact with the cooperating surface in the extended position of the prosthesis but only partial contact in the flexed position of the prosthesis.
3. A prosthesis according to claim 2, characterized in that the body of rotation is an adjustable eccentric connected to the flexing-axis pin.
4. A prosthesis according to claim 2, characterised in that said first part further comprises fork arms for receiving said flexing-axis pin, said pin being secured to said fork arms by screwthreaded pins in order to prevent relative displacement and rotation between said body of rotation and said first part.
5. A prosthesis according to claim 1, characterised in that the flexing-axis pin is mounted relatively to the first part and intermediate element, and the latter is mounted relatively to the pivot and said second part, in each case by means of at least one plastics bearing element.
6. A prosthesis according to claim 5, characterised in that the plastics bearing elements are replaceable.
7. A prothesis according to claim 5, characterised in that the bearing elements for the flexing-axis pin is a flanged sleeve combined from two parts.
8. A prosthesis according to claim 1, characterised in that a plastics runner is disposed on said intermediate element and the range of said flexing angle is determined in one direction by the abutment of said first part against said intermediate element and in the other direction by the abutment of said first part with said plastics runner.
9. A prosthesis according to claim 3, characterised in that the eccentric and that part of the pivot which is near the eccentric are enclosed in dust-tight manner.
10. A prosthesis according to claim 1, characterised in that the securing element is a screw which is preferably self-locking, is screwed into a projection of the intermediate element and engages at its exposed inner end in an annular groove in the pivot.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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DE2549318 | 1975-11-04 | ||
DE2549318A DE2549318C3 (en) | 1975-11-04 | 1975-11-04 | Knee joint prosthesis |
Publications (1)
Publication Number | Publication Date |
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US4112522A true US4112522A (en) | 1978-09-12 |
Family
ID=5960810
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
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US05/738,978 Expired - Lifetime US4112522A (en) | 1975-11-04 | 1976-11-04 | Knee-joint prosthesis |
Country Status (6)
Country | Link |
---|---|
US (1) | US4112522A (en) |
CH (1) | CH610756A5 (en) |
DD (1) | DD127245A5 (en) |
DE (1) | DE2549318C3 (en) |
FR (1) | FR2330375A1 (en) |
GB (1) | GB1566438A (en) |
Cited By (25)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4293963A (en) * | 1980-02-14 | 1981-10-13 | Zimmer Usa, Inc. | Unrestrained elbow prosthesis |
US4352212A (en) * | 1979-03-05 | 1982-10-05 | Howmedica, Inc. | Joint prosthesis |
US4383337A (en) * | 1980-10-22 | 1983-05-17 | Zimmer Usa, Inc. | Elbow prosthesis |
EP0083155A1 (en) * | 1981-12-07 | 1983-07-06 | Dow Corning Corporation | Shock absorbing stop for prosthetic devices |
US4538305A (en) * | 1981-05-19 | 1985-09-03 | Gmt Gesellschaft Fur Medizinische Technik Mbh | Articulated prosthesis |
US4770660A (en) * | 1987-01-20 | 1988-09-13 | Osteonics Corp. | Femoral prosthesis with selectively removable collar |
US4822364A (en) * | 1987-12-21 | 1989-04-18 | New York Society For The Relief Of The Ruptured And Crippled, Maintaining The Hospital For Special Surgery | Elbow joint prosthesis |
US4834758A (en) * | 1988-05-26 | 1989-05-30 | New York Society For The Relief Of The Ruptured And Crippled, Maintaining The Hospital For Special Surgery | Bone prosthesis for the leg and thigh |
US4865606A (en) * | 1987-08-13 | 1989-09-12 | Friedrichsfeld Gmbh Keramik Und Kunststoffwerke | Endoprosthesis for a knee-joint |
US4923472A (en) * | 1988-01-22 | 1990-05-08 | Salus S.R.L. | Artificial knee-joint |
US5370701A (en) * | 1990-09-28 | 1994-12-06 | Arch Development Corporation | Rotating/sliding contrained prosthetic knee |
US5413608A (en) * | 1992-09-24 | 1995-05-09 | Waldemar Link Gmbh & Co. | Knee joint endoprosthesis for replacing the articular surfaces of the tibia |
US5458644A (en) * | 1991-12-18 | 1995-10-17 | Eska Medical Gmbh & Co. | Knee joint endoprosthesis |
US5507830A (en) * | 1989-02-08 | 1996-04-16 | Smith & Nephew Richards Inc. | Modular hip prosthesis |
US5921358A (en) * | 1994-10-07 | 1999-07-13 | Gramtec Innovation Ab | Rotation damper in a toggle joint prosthesis |
US5954770A (en) * | 1996-02-21 | 1999-09-21 | Plus Endoprothetik Ag | Endoprosthetic knee joint |
US6485519B2 (en) | 2001-01-29 | 2002-11-26 | Bristol-Myers Squibb Company | Constrained prosthetic knee with rotating bearing |
US20030208280A1 (en) * | 2000-04-21 | 2003-11-06 | Behrooz Tohidi | Wear resistant artificial joint |
US6719800B2 (en) | 2001-01-29 | 2004-04-13 | Zimmer Technology, Inc. | Constrained prosthetic knee with rotating bearing |
US6773461B2 (en) | 2001-01-29 | 2004-08-10 | Zimmer Technology, Inc. | Constrained prosthetic knee with rotating bearing |
US20100249940A1 (en) * | 2009-01-23 | 2010-09-30 | Zimmer, Inc. | Posterior-stabilized total knee prosthesis |
US20120136452A1 (en) * | 2009-07-10 | 2012-05-31 | Medizinische Hochschule Hannover | Knee joint prosthesis and related method |
US8545571B2 (en) | 2010-07-30 | 2013-10-01 | Howmedica Osteonics Corp. | Stabilized knee prosthesis |
US9132014B2 (en) | 2010-04-13 | 2015-09-15 | Zimmer, Inc. | Anterior cruciate ligament substituting knee implants |
US9662217B2 (en) | 2011-07-13 | 2017-05-30 | Zimmer Gmbh | Femoral knee prosthesis with diverging lateral condyle |
Families Citing this family (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4301553A (en) * | 1975-08-15 | 1981-11-24 | United States Surgical Corporation | Prosthetic knee joint |
DE2549819C3 (en) * | 1975-11-06 | 1982-04-29 | Sanitätshaus Schütt & Grundei, Werkstätten für Orthopädie-Technik, 2400 Lübeck | Endoprosthesis for a knee joint |
GB1582974A (en) * | 1975-11-06 | 1981-01-21 | Schuett & Grundei Sanitaet | Finger joint endoprostheses |
FR2568467B1 (en) * | 1984-08-06 | 1989-06-23 | Benoist Girard Cie | KNEE JOINT PROSTHESIS. |
DE3431645A1 (en) * | 1984-08-29 | 1986-03-13 | GMT GESELLSCHAFT FüR MEDIZINISCHE TECHNIK MBH | ENDOPROTHESIS |
US4714472A (en) * | 1987-01-20 | 1987-12-22 | Osteonics Corp. | Knee prosthesis with accommodation for angular misalignment |
US5007933A (en) * | 1989-01-31 | 1991-04-16 | Osteonics Corp. | Modular knee prosthesis system |
DE4002424A1 (en) * | 1989-07-26 | 1991-02-07 | Orthoplant Endoprothetik | Knee joint prosthesis with femur shells and tibia plate - has lug on connecting component sliding freely in axial direction |
FR2685631A1 (en) * | 1991-12-31 | 1993-07-02 | Cuilleron J | Intracondylar total knee prosthesis |
ATE202465T1 (en) * | 1995-01-31 | 2001-07-15 | Sulzer Orthopaedie Ag | JOINT PROSTHESIS, IN PARTICULAR KNEE JOINT PROSTHESIS |
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DE2154338A1 (en) * | 1971-11-02 | 1973-05-17 | Eduard Hartmann | JOINT PROSTHESIS |
US3813700A (en) * | 1973-04-16 | 1974-06-04 | S Tennant | Prosthetic knee device |
US3909854A (en) * | 1973-05-03 | 1975-10-07 | Ysidore M Martinez | Knee implant prosthesis |
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US4001896A (en) * | 1975-06-09 | 1977-01-11 | Zimmer, U.S.A. Inc. | Prosthetic joint for total knee replacement |
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DE2114287C3 (en) * | 1971-03-24 | 1974-03-21 | Fa. Waldemar Link, 2000 Hamburg | Joint prosthesis for the replacement of bone tissue in the area of the knee joint of a person |
DE2310113C2 (en) * | 1973-03-01 | 1974-11-07 | Blietz, Rudolf, Dr.Med.Habil., 2800 Bremen | Knee joint endoprosthesis |
GB1514479A (en) * | 1974-10-01 | 1978-06-14 | Elson R | Prosthetic joints |
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1975
- 1975-11-04 DE DE2549318A patent/DE2549318C3/en not_active Expired
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1976
- 1976-10-27 CH CH1351576A patent/CH610756A5/xx not_active IP Right Cessation
- 1976-11-02 GB GB45611/76A patent/GB1566438A/en not_active Expired
- 1976-11-03 DD DD195577A patent/DD127245A5/xx unknown
- 1976-11-04 US US05/738,978 patent/US4112522A/en not_active Expired - Lifetime
- 1976-11-04 FR FR7633299A patent/FR2330375A1/en active Granted
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DE2154338A1 (en) * | 1971-11-02 | 1973-05-17 | Eduard Hartmann | JOINT PROSTHESIS |
US3813700A (en) * | 1973-04-16 | 1974-06-04 | S Tennant | Prosthetic knee device |
US3909854A (en) * | 1973-05-03 | 1975-10-07 | Ysidore M Martinez | Knee implant prosthesis |
US3934272A (en) * | 1974-11-19 | 1976-01-27 | The University Of Melbourne | Knee prosthesis |
US4001896A (en) * | 1975-06-09 | 1977-01-11 | Zimmer, U.S.A. Inc. | Prosthetic joint for total knee replacement |
Cited By (39)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4352212A (en) * | 1979-03-05 | 1982-10-05 | Howmedica, Inc. | Joint prosthesis |
US4293963A (en) * | 1980-02-14 | 1981-10-13 | Zimmer Usa, Inc. | Unrestrained elbow prosthesis |
US4383337A (en) * | 1980-10-22 | 1983-05-17 | Zimmer Usa, Inc. | Elbow prosthesis |
US4538305A (en) * | 1981-05-19 | 1985-09-03 | Gmt Gesellschaft Fur Medizinische Technik Mbh | Articulated prosthesis |
EP0083155A1 (en) * | 1981-12-07 | 1983-07-06 | Dow Corning Corporation | Shock absorbing stop for prosthetic devices |
US4770660A (en) * | 1987-01-20 | 1988-09-13 | Osteonics Corp. | Femoral prosthesis with selectively removable collar |
US4865606A (en) * | 1987-08-13 | 1989-09-12 | Friedrichsfeld Gmbh Keramik Und Kunststoffwerke | Endoprosthesis for a knee-joint |
US4822364A (en) * | 1987-12-21 | 1989-04-18 | New York Society For The Relief Of The Ruptured And Crippled, Maintaining The Hospital For Special Surgery | Elbow joint prosthesis |
US4923472A (en) * | 1988-01-22 | 1990-05-08 | Salus S.R.L. | Artificial knee-joint |
US4834758A (en) * | 1988-05-26 | 1989-05-30 | New York Society For The Relief Of The Ruptured And Crippled, Maintaining The Hospital For Special Surgery | Bone prosthesis for the leg and thigh |
US5507830A (en) * | 1989-02-08 | 1996-04-16 | Smith & Nephew Richards Inc. | Modular hip prosthesis |
US5370701A (en) * | 1990-09-28 | 1994-12-06 | Arch Development Corporation | Rotating/sliding contrained prosthetic knee |
US5458644A (en) * | 1991-12-18 | 1995-10-17 | Eska Medical Gmbh & Co. | Knee joint endoprosthesis |
US5413608A (en) * | 1992-09-24 | 1995-05-09 | Waldemar Link Gmbh & Co. | Knee joint endoprosthesis for replacing the articular surfaces of the tibia |
US5921358A (en) * | 1994-10-07 | 1999-07-13 | Gramtec Innovation Ab | Rotation damper in a toggle joint prosthesis |
US5954770A (en) * | 1996-02-21 | 1999-09-21 | Plus Endoprothetik Ag | Endoprosthetic knee joint |
US20030208280A1 (en) * | 2000-04-21 | 2003-11-06 | Behrooz Tohidi | Wear resistant artificial joint |
US6719800B2 (en) | 2001-01-29 | 2004-04-13 | Zimmer Technology, Inc. | Constrained prosthetic knee with rotating bearing |
US6773461B2 (en) | 2001-01-29 | 2004-08-10 | Zimmer Technology, Inc. | Constrained prosthetic knee with rotating bearing |
US20040249467A1 (en) * | 2001-01-29 | 2004-12-09 | Meyers John E. | Constrained prosthetic knee with rotating bearing |
US8268006B2 (en) | 2001-01-29 | 2012-09-18 | Zimmer, Inc. | Constrained prosthetic knee with rotating bearing |
USRE44476E1 (en) | 2001-01-29 | 2013-09-03 | Zimmer, Inc. | Constrained prosthetic knee with rotating bearing |
US6485519B2 (en) | 2001-01-29 | 2002-11-26 | Bristol-Myers Squibb Company | Constrained prosthetic knee with rotating bearing |
US8888857B2 (en) | 2001-01-29 | 2014-11-18 | Zimmer, Inc. | Constrained prosthetic knee with rotating bearing |
US9615929B2 (en) | 2009-01-23 | 2017-04-11 | Zimmer, Inc. | Posterior-stabilized total knee prosthesis |
US20100249940A1 (en) * | 2009-01-23 | 2010-09-30 | Zimmer, Inc. | Posterior-stabilized total knee prosthesis |
US10076420B2 (en) | 2009-01-23 | 2018-09-18 | Zimmer, Inc. | Posterior-stabilized total knee prosthesis |
US9999512B2 (en) | 2009-07-10 | 2018-06-19 | Aesculap Ag | Knee joint prosthesis and related method |
US9833323B2 (en) * | 2009-07-10 | 2017-12-05 | Aesculap Ag | Knee joint prosthesis and related method |
US20120136452A1 (en) * | 2009-07-10 | 2012-05-31 | Medizinische Hochschule Hannover | Knee joint prosthesis and related method |
US9132014B2 (en) | 2010-04-13 | 2015-09-15 | Zimmer, Inc. | Anterior cruciate ligament substituting knee implants |
US9861484B2 (en) | 2010-04-13 | 2018-01-09 | Zimmer, Inc. | Anterior cruciate ligament substituting knee implants |
US10667919B2 (en) | 2010-04-13 | 2020-06-02 | Zimmer, Inc. | Anterior cruciate ligament substituting knee implants |
US11986394B2 (en) | 2010-04-13 | 2024-05-21 | Zimmer, Inc. | Anterior cruciate ligament substituting knee implants |
US9452051B2 (en) | 2010-07-30 | 2016-09-27 | Howmedica Osteonics Corp. | Stabilized knee prosthesis |
US8545571B2 (en) | 2010-07-30 | 2013-10-01 | Howmedica Osteonics Corp. | Stabilized knee prosthesis |
US10376371B2 (en) | 2010-07-30 | 2019-08-13 | Howmedica Osteonics Corp. | Stabilized knee prosthesis |
US11229521B2 (en) | 2010-07-30 | 2022-01-25 | Howmedica Osteonics Corp. | Stabilized knee prosthesis |
US9662217B2 (en) | 2011-07-13 | 2017-05-30 | Zimmer Gmbh | Femoral knee prosthesis with diverging lateral condyle |
Also Published As
Publication number | Publication date |
---|---|
GB1566438A (en) | 1980-04-30 |
DD127245A5 (en) | 1977-09-14 |
FR2330375B1 (en) | 1981-06-12 |
CH610756A5 (en) | 1979-05-15 |
FR2330375A1 (en) | 1977-06-03 |
DE2549318B2 (en) | 1981-02-26 |
DE2549318A1 (en) | 1977-05-05 |
DE2549318C3 (en) | 1981-10-29 |
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